A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form

A61L2300/606—Coatings

Abstract

Provided herein is a poly(ester amide) (PEA) polymer blend and coatings and medical devices formed of the blend.

Description

CROSS REFERENCE TO RELATED APPLICATION

This is a continuation application of U.S. application Ser. No. 10/960,381, filed on Oct. 6, 2004 now U.S. Pat. No. 7,166,680, the teaching of which is incorporated herein in its entirety.

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention generally relates to blends of poly(ester amide) (PEA) polymers or copolymers with a low glass transition temperature (Tg) and PEA polymers or copolymers with a high Tg, which are useful for coating an implantable device such as a drug-delivery stent.

2. Description of the Background

Poly(ester amide) polymers are known for their relatively low glass transition temperatures. For example, co-poly-{[N,N′-sebacoyl-bis-(L-leucine)-1,6-hexylene diester]-[N,N′-sebacoyl-L-lysine benzyl ester]} (PEA-Bz) and co-poly{[N,N′-sebacoyl-bis-(L-leucine)-1,6-hexylene, diester]-[N,N′-sebacoyl-L-lysine 2,2,6,6-tetramethyl-4-amino-1-piperidinyloxyl amide]} (PEA-TEMPO) have a Tg of approximately 23° C. and 33° C., respectively.

Complications related to low Tg manifest themselves as reduced drug release rate control, increased polymer degradation rate, reduced shelf life stability, and potentially increased system mechanical failures. Low Tg materials usually have higher drug permeabilities, which necessitates the use of greater amounts of polymer to control release rate of the drug. Moreover, the low Tg enables the drug to diffuse within the coating. In other words, the drug distribution within a given coating can change with time until an equilibrium state is reached, resulting in release rate shifts. Low Tg materials also tend to be softer, they can be more adhesive to balloons, and are more prone to failure during mechanical perturbations such as crimping and expansion.

The embodiments of the present invention provide for methods addressing these issues.

SUMMARY OF THE INVENTION

Provided herein are polymer blends that include poly(ester amide) (PEA) polymers or copolymers with a low Tg and PEA polymers or copolymers with a high Tg. The polymer blends provided herein can form coatings that have improved stability, drug release rate, and mechanical characteristics. The polymer blends can be fine-tuned to have different polymer degradation rates in that, as the effective Tg of the polymer blend is increased, the degradation rate of the polymer blend will decrease.

The PEA polymer blend has an effective Tg equal to or above the Tg of PEA-Bz. In some embodiments, the PEA polymer blend has an effective Tg of about 23° C. or above. The PEA polymer blends described herein can be used to coat an implantable device or to form the implantable device itself, one example of which is a stent. In some embodiments, the PEA polymer blends can be used optionally with a biobeneficial material and/or optionally a bioactive agent to coat an implantable device. In some other embodiments, the PEA polymer blends can be used with one or more biocompatible polymers, which can be biodegradable, bioabsorbable, non-degradable, or non-bioabsorbable polymer.

The implantable device can be a stent that can be a metallic, biodegradable or nondegradable stent. The stent can be intended for neurovasculature, carotid, coronary, puhnonary, aorta, renal, biliary, iliac, femoral, popliteal, or other peripheral vasculature. The stent can be used to treat or prevent a disorder such as atherosclerosis, thrombosis, restenosis, hemorrhage, vascular dissection or perforation, vascular aneurysm, vulnerable plaque, chronic total occlusion, claudication, anastomotic proliferation for vein and artificial grafts, bile duct obstruction, ureter obstruction, tumor obstruction, or combinations thereof.

DETAILED DESCRIPTION

Provided herein are polymer blends that include poly(ester amide) (PEA) polymers or copolymers with a low Tg and PEA polymers or copolymers with a high Tg. The polymer blends provided herein can form coatings that have improved stability, drug release rate, and mechanical characteristics. The polymer blends can be fine-tuned to have different polymer degradation rates in that, as the effective Tg of the polymer blend is increased, the degradation rate of the polymer blend will decrease.

Tg as used herein generally refers to the temperature at which the amorphous domains of a polymer change from a brittle vitreous state to a plastic state at atmospheric pressure. In other words, Tg corresponds to the temperature where the onset of segmental motion in the chains of the polymer occurs, and it is discernible in a heat-capacity-versus-temperature graph for a polymer. When an amorphous or semicrystalline polymer is heated, its coefficient of expansion and heat capacity both increase as the temperature rises, indicating increased molecular motion. As the temperature rises, the polymer's actual molecular volume remains constant. Therefore, a higher coefficient of expansion points to a free volume increase of the system and increased freedom of movement for the molecules. The term “low Tg” refers to a Tg of a low Tg material (generally below about 30° C.), e.g., the Tg of PEA-Bz, which has a structure of
—[-sebacinate-L-Leu-hexanediol-L-Leu-]m-[-sebacinate-Lys benzyl ester-]n— Formula 1
where m and n are independent positive integers ranging from, e.g., 1 to 100,000.

The PEA polymers forming the blend are substantially mutually soluble in that. one polymer has a solubility of at least about 1 wt %, at least about 5 wt %, at least about 10 wt %, at least about 20 wt %, at least about 50 wt %, at least about 75 wt %, at least about 90 wt %, or at least about 99 wt % in the other polymer and vice versa. In some embodiments, the PEA polymers forming the blend can be substantially thermodynamically miscible, for example, the PEA polymers forming the polymer blend will not phase-separate into microdomains. In some other embodiments, the PEA polymers forming the blend may be mechanically compatible. Mechanically compatible blends are composite systems where the mechanical properties of the blend are not degraded or improved when compared to the individual components that make up the blend as a result of relatively uniform and consistent microphase separation. In contrast, mechanically incompatible blends have degraded mechanical properties when compared to the properties of the individual components as a result of exhibiting gross phase separation. Mechanically incompatible blends typically exhibit low elongation and brittle failure.

The PEA polymer blend has an effective Tg equal to or above the Tg of PEA-Bz. As used herein, the term “effective Tg” refers to the Tg of a blend of materials having different Tgs. In some embodiments, the PEA polymer blend has an effective Tg of about 23° C. or above. However, raising the effective Tg too high will result in a loss of mechanical integrity, and potentially too low a drug release rate. A preferred range of the effective Tg of the PEA polymer blend is in the range, for example, between about 23° C. and about 75° C. The effective Tg of a thermodynamically compatible polymer blend can be calculated according to the formula 1/Tg mix=W1/Tg1+W2/Tg2, where Tg mix is the glass transition of the blend, while W1, W2, Tg1 and Tg2 are the weight fractions and glass transition temperatures of each of the components. For more than 2 components, this equation can be generalized as: 1/Tg mix=ΣWi/Tgi where Σ represents the summation of i components. Alternatively, the formula is often represented as follows: Tg mix=φ1Tg1+φ2Tg2, where φ represents the volume fraction of each component.

The PEA polymer blends described herein can be used to coat an implantable device or to form the implantable device itself, one example of which is a stent. In some embodiments, the PEA polymer blends can be used optionally with a biobeneficial material and/or optionally a bioactive agent to coat an implantable device. In some other embodiments, the PEA polymer blends can be used with one or more biocompatible polymers, which can be biodegradable, bioabsorbable, non-degradable, or non-bioabsorbable polymers.

The implantable device can be a stent that can be metallic, biodegradable or nondegradable. The stent can be intended for neurovasculature, carotid, coronary, pulmonary, aortic, renal, biliary, iliac, femoral, popliteal, or other peripheral vasculature. The stent can be used to treat or prevent a disorder such as atherosclerosis, thrombosis, restenosis, hemorrhage, vascular dissection or perforation, vascular aneurysm, vulnerable plaque, chronic total occlusion, claudication, anastomotic proliferation for vein and artificial grafts, bile duct obstruction, ureter obstruction, tumor obstruction, or combinations thereof.

Modification of Poly(Ester Amide) (PEA) Polymers

In some embodiments, PEA polymers with a high Tg can be formed by modifying a PEA polymer having at least one ester grouping and at least one amide grouping in the backbone that has a low Tg. In one embodiment, the low Tg polymer can be a PEA having three building blocks: an amino acid, a diol, and a diacid. The diacid is preferably a C2-C12 diacid, aliphatic or with unsaturation. The amino acid can be, for example, glycine, valine, alanine, proline, glutamine, methionine, leucine, isoleucine, or phenylalanine. An optional second amino acid may be included. The second amino acid can be, for example, lysine, tyrosine, tryptophan, arginine, histidine, glutamic acid, aspartic acid, threonine, serine, or cysteine. The second amino acid may contain a side group to enable the attachment of pharmacologically active compounds or property modifiers. PEA polymers with various thermal properties can be readily prepared by varying these components during synthesis.

Generally, decreasing the polymethylene chain length of the diol or diacid building block will increase the Tg. PEA polymers based on amino acids with optical rotation (e.g., L-isomers) will have higher Tg than those based on the corresponding racemic amino acids (D,L-isomers). PEA polymers synthesized from optically active L-amino acids with symmetrical side substituents (e.g., valine, leucine, phenylalanine) will have higher Tgs than those synthesized from L-amino acids with nonsymmetrical side substituents (e.g., isoleucine). Amino acids with aromatic substituents (e.g., phenylalanine) tend to have higher Tgs.

In one embodiment, the PEA polymer with a low Tg can be PEA-Bz. PEA-Bz can be modified to replace a side group or a backbone group thereof to increase the Tg of the polymer. Some strategies of modifying PEA-Bz to increase Tg are described below.

(1) In PEA-Bz, when the benzyl ester that conjugates to the lysine side group is replaced with TEMPO, the Tg of the resultant PEA polymer, PEA-TEMPO, is increased by 10° C. PEA-TEMPO has a formula of
—[-sebacinate-L-Leu-hexanediol-L-Leu-]m-[-sebacinate-Lys TEMPO-]n— Formula 2

(2) Removing the optional second amino acid (Lys) from PEA-Bz (Tg=23° C.), which forms
—[-sebacinate-L-Leu-hexanediol-L-Leu-]n— Formula 3
increases the Tg of the polymer by 14° C.

(3) Decreasing the polymethylene chain length of either the diol or the diacid further increases the Tg. For example, the sebacinate in the PEA of formula 3 can be replaced with adipate to form a PEA polymer (Formula 4A) with a Tg of 38° C., the hexanediol in formula 3 is replaced with butanediol to form a PEA polymer (Formula 4B) with a Tg of 47° C., and both the sebacinate or hexanediol in formula 3 can be replaced with adipate and butanediol, respectively, to form a PEA polymer with a Tg of 45° C.:
—[-adipate-L-Leu-hexanediol-L-Leu-]n— Formula 4A
—[-sebacinate-L-Leu-butanediol-L-Leu-]n— Formula 4B
—[-adipate-L-Leu-butanediol-L-Leu-]n— Formula 4C

(4) The effect of optically active amino acids, e.g., an L-isomer, with symmetrical side substituents, which supposedly would result in polymers with higher Tgs, depends on the polymethylene chain lengths of the diol and/or diacid. With long chain length diols and diacids, the Tgs of the modified PEA polymers are similar to that of the unmodified PEA polymer. For example, the L-leucine of Formula 3 can be replaced with L-valine to form a PEA of Formula 5A with a Tg of 33° C. or L-phenylalanine to form a PEA of Formula 5B with a Tg of 35° C.
—[-sebacinate-L-Val-hexanediol-L-Val-]n— Formula 5A
—[-sebacinate-L-Phe-hexanediol-L-Phe-]n— Formula 5B
With shorter chain length diols and/or diacids, wider variations in Tg can be obtained. For example, the PEA of Formula 4C can be modified by replacing the L-leucine in the formula with L-valine or L-phenylalanine to generate PEAs of Formulae 5C and 5D with Tgs of 58° C. and 59° C., respectively. Moreover, the phenylalanine based PEA is semicrystalline, having a melting temperature (Tm) of 104° C.
—[-adipate-L-Val-butanediol-L-Val-]n— Formula 5C
—[-adipate-L-Phe-butanediol-L-Phe-]n— Formula 5D

In another embodiment, PEA polymers with a high Tg can retain the lysine moiety of the PEA of formulae 1 or 2, using shorter chain length diacids and/or diols. Some examples of these PEA polymers are given below:
—[-adipate-L-Leu-hexanediol-L-Leu-]m-[-adipate-Lys-R]n—R=benzyl ester or TEMPO Formula 6A
—[-sebacinate-L-Leu-butanediol-L-Leu-]m-[-sebacinate-Lys-R]n—R=benzyl ester or TEMPO Formula 6B
—[-adipate-L-Leu-butanediol-L-Leu-]m-[-adipate-Lys-R]n—R=benzyl ester or TEMPO Formula 6C
—[-sebacinate-L-Val-hexanediol-L-Val-]m-[-sebacinate-Lys-R]n—R=benzyl ester or TEMPO Formula 6D
—[-sebacinate-L-Phe-hexanediol-L-Phe-]m-[sebacinate-Lys-R]n—R=benzyl ester or TEMPO Formula 6E
—[-adipate-L-Val-butanediol-L-Val-]m-[-adipate-Lys-R]n—R=benzyl ester or TEMPO Formula 6F
—[-adipate-L-Phe-butanediol-L-Phe-]m-[-adipate-Lys-R]n—R=benzyl ester or TEMPO Formula 6G

In a further embodiment, the PEA polymer of formulae 1 or 2 can be modified by conjugating a group other than benzyl ester or TEMPO to the lysine block to increase the Tg of the polymer. For example, a short chain alcohol such as methanol, ethanol or propanol can be used instead of benzyl alcohol, and the resultant PEA polymer is
—[-sebacinate-L-Leu-hexanediol-L-Leu-]m-[-sebacinate-Lys R]n—R=methyl, ethyl, or propyl Formula 7
In general, if a moiety or group smaller than benzyl ester is conjugated to the lysine block, the resultant PEA polymer would have a higher Tg than PEA-Bz. Therefore, the polymer of Formula 7 where R is methyl, ethyl or propyl is expected to have a higher Tg than PEA-Bz.

The PEA polymers described herein can be made by condensation polymerization using, among others, diamino subunits and dicarboxylic acids. The preparation of one example of these PEAs is shown in Scheme I, where the dicarboxylic acid is converted to an active di-p-nitrophenyl derivative.

PEA Polymer Blends

In some embodiments, the PEA polymers with a high Tg can be blended with PEA-Bz or PEA-TEMPO. In one embodiment, the PEA with a high Tg does not contain a lysine block. The side group on the lysine block in PEA-Bz or PEA-TEMPO can be conjugated with or attached to another moiety or an active agent.

In another embodiment, the PEA blend can be a blend of a PEA-Bz or PEA-TEMPO having one ratio of lysine to leucine with a second PEA-Bz or PEA-TEMPO having a different ratio of lysine to leucine. One example can be a blend formed of PEA-Bz or PEA-TEMPO having a ratio of 3/1 of the leucine block to lysine block and a PEA-Bz or PEA-TEMPO having a higher ratio of the leucine block to lysine block. A higher ratio of the leucine block to lysine block in PEA-Bz or PEA-TEMPO would increase the Tg of the polymer.

In a further embodiment, the PEA blend can be formed of a PEA polymer having a ratio of 3/1 of the leucine block to the lysine block with a moiety other than benzyl alcohol or TEMPO conjugated to lysine and a PEA polymer of Formulae 1 or 2.

The PEA polymer blend defined above can further include one or more biocompatible polymers, defined below, which are not PEA polymers.

In some other embodiments, the modified PEA polymers and/or PEA-Bz or PEA-TEMPO can be blended with one or more biocompatible polymers, which are not PEA polymers. Because of the desirability of having a Tg above the Tg of PEA-Bz or PEA-TEMPO, as discussed, when the biocompatible polymer is blended with PEA-Bz and/or PEA-TEMPO, the biocompatible polymer would need to have a Tg higher than that of PEA-Bz or PEA-TEMPO and need to be substantially miscible, which is defined above, with the PEA-Bz and/or PEA-TEMPO. The biocompatible polymer is defined below.

Biocompatible Polymer

The biocompatible polymer useful for forming the PEA polymer blend defined herein can be any biocompatible polymer known in the art, which can be biodegradable or nondegradable.

In some other embodiments, the biocompatible polymer can exclude any one or more of the polymers provided above.

The biocompatible polymer can provide a controlled release of a bioactive agent, if included in the coating and/or if binding the bioactive agent to a substrate, which can be the surface of an implantable device or a coating thereon. Controlled release and delivery of bioactive agent using a polymeric carrier has been extensively researched in the past several decades (see, for example, Mathiowitz, Ed., Encyclopedia of Controlled Drug Delivery, C.H.I.P.S., 1999). For example, PLA based drug delivery systems have provided controlled release of many therapeutic drugs with various degrees of success (see, for example, U.S. Pat. No. 5,581,387 to Labrie, et al.). The release rate of the bioactive agent can be controlled by, for example, selection of a particular type of biocompatible polymer, which can provide a desired release profile of the bioactive agent. The release profile of the bioactive agent can be further controlled by selecting the molecular weight of the biocompatible polymer and/or the ratio of the biocompatible polymer to the bioactive agent. One of ordinary skill in the art can readily select a carrier system using a biocompatible polymer to provide a controlled release of the bioactive agent.

A preferred biocompatible polymer is a polyester, such as one of PLA, PLGA, PGA, PHA, poly(3-hydroxybutyrate) (PHB), poly(3-hydroxybutyrate-co-3-hydroxyvalerate), poly((3-hydroxyvalerate), poly(3-hydroxyhexanoate), poly(4-hydroxybutyrate), poly(4-hydroxyvalerate), poly(4-hydroxyhexanoate), and a combination thereof, and polycaprolactone (PCL).

Bioactive Agents

The PEA polymer blends described herein can form a coating with one or more bioactive agents. These bioactive agents can be any agent which is a therapeutic, prophylactic, or diagnostic agent. These agents can have anti-proliferative or anti-inflammmatory properties or can have other properties such as antineoplastic, antiplatelet, anti-coagulant, anti-fibrin, antithrombonic, antimitotic, antibiotic, antiallergic, antioxidant as well as cystostatic agents. Examples of suitable therapeutic and prophylactic agents include synthetic inorganic and organic compounds, proteins and peptides, polysaccharides and other sugars, lipids, and DNA and RNA nucleic acid sequences having therapeutic, prophylactic or diagnostic activities. Nucleic acid sequences include genes, antisense molecules which bind to complementary DNA to inhibit transcription, and ribozymes. Some other examples of other bioactive agents include antibodies, receptor ligands, enzymes, adhesion peptides, blood clotting factors, inhibitors or clot dissolving agents such as streptokinase and tissue plasminogen activator, antigens for immunization, hormones and growth factors, oligonucleotides such as antisense oligonucleotides and ribozymes and retroviral vectors for use in gene therapy. Examples of anti-proliferative agents include rapamycin and its functional or structural derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), and its functional or structural derivatives, paclitaxel and its functional and structural derivatives. Examples of rapamycin derivatives include methyl rapamycin (ABT-578), 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, and 40-O-tetrazole-rapamycin. Examples of paclitaxel derivatives include docetaxel. Examples of antineoplastics and/or antimitotics include methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia & Upjohn, Peapack N.J.), and mitomycin (e.g. Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein IIb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, thrombin inhibitors such as Angiomax ä (Biogen, Inc., Cambridge, Mass.), calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck & Co., Inc., Whitehouse Station, N.J.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), nitric oxide or nitric oxide donors, super oxide dismutases, super oxide dismutase mimetic, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), estradiol, anticancer agents, dietary supplements such as various vitamins, and a combination thereof. Examples of anti-inflammatory agents including steroidal and non-steroidal anti-inflammatory agents include tacrolimus, dexamethasone, clobetasol, combinations thereof. Examples of such cytostatic substance include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g. Prinivil® and Prinzide® from Merck & Co., Inc., Whitehouse Station, N.J.). An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate include alpha-interferon, bioactive RGD, and genetically engineered epithelial cells. The foregoing substances can also be used in the form of prodrugs or co-drugs thereof. The foregoing substances are listed by way of example and are not meant to be limiting. Other active agents which are currently available or that may be developed in the future are equally applicable.

The dosage or concentration of the bioactive agent required to produce a favorable therapeutic effect should be less than the level at which the bioactive agent produces toxic effects and greater than the level at which non-therapeutic results are obtained. The dosage or concentration of the bioactive agent required to inhibit the desired cellular activity of the vascular region can depend upon factors such as the particular circumstances of the patient; the nature of the trauma; the nature of the therapy desired; the time over which the ingredient administered resides at the vascular site; and if other active agents are employed, the nature and type of the substance or combination of substances. Therapeutic effective dosages can be determined empirically, for example by infusing vessels from suitable animal model systems and using immunohistochemical, fluorescent or electron microscopy methods to detect the agent and its effects, or by conducting suitable in vitro studies. Standard pharmacological test procedures to determine dosages are understood by one of ordinary skill in the art.

Examples of Implantable Device

As used herein, an implantable device may be any suitable medical substrate that can be implanted in a human or veterinary patient. Examples of such implantable devices include self-expandable stents, balloon-expandable stents, stent-grafts, grafts (e.g., aortic grafts), artificial heart valves, cerebrospinal fluid shunts, pacemaker electrodes, and endocardial leads (e.g., FINELINE and ENDOTAK, available from Guidant Corporation, Santa Clara, Calif.). The underlying structure of the device can be of virtually any design. The device can be made of a metallic material or an alloy such as, but not limited to, cobalt chromium alloy (ELGILOY), stainless steel (316L), high nitrogen stainless steel, e.g., BIODUR 108, cobalt chrome alloy L-605, “MP35N,” “MP20N,” ELASTINITE (Nitinol), tantalum, nickel-titanium alloy, platinum-iridium alloy, gold, magnesium, or combinations thereof “MP35N” and “MP20N” are trade names for alloys of cobalt, nickel, chromium and molybdenum available from Standard Press Steel Co., Jenkintown, Pa. “MP35N” consists of 35% cobalt, 35% nickel, 20% chromium, and 10% molybdenum. “MP20N” consists of 50% cobalt, 20% nickel, 20% chromium, and 10% molybdenum. Devices made from bioabsorbable or biostable polymers could also be used with the embodiments of the present invention.

Method of Use

In accordance with embodiments of the invention, a coating of the polymer blends of the various described embodiments can be formed on an implantable device or prosthesis, e.g., a stent. For coatings including one or more active agents, the agent will retain on the medical device such as a stent during delivery and expansion of the device, and released at a desired rate and for a predetermined duration of time at the site of implantation. Preferably, the medical device is a stent. A stent having the above-described coating is useful for a variety of medical procedures, including, by way of example, treatment of obstructions caused by tumors in bile ducts, esophagus, trachea/bronchi and other biological passageways. A stent having the above-described coating is particularly useful for treating occluded regions of blood vessels caused by abnormal or inappropriate migration and proliferation of smooth muscle cells, thrombosis, and restenosis. Stents may be placed in a wide array of blood vessels, both arteries and veins. Representative examples of sites include the iliac, renal, and coronary arteries.

For implantation of a stent, an angiogram is first performed to determine the appropriate positioning for stent therapy. An angiogram is typically accomplished by injecting a radiopaque contrasting agent through a catheter inserted into an artery or vein as an x-ray is taken. A guidewire is then advanced through the lesion or proposed site of treatment. Over the guidewire is passed a delivery catheter, which allows a stent in its collapsed configuration to be inserted into the passageway. The delivery catheter is inserted either percutaneously or by surgery into the femoral artery, brachial artery, femoral vein, or brachial vein, and advanced into the appropriate blood vessel by steering the catheter through the vascular system under fluoroscopic guidance. A stent having the above-described coating may then be expanded at the desired area of treatment. A post-insertion angiogram may also be utilized to confirm appropriate positioning.

EXAMPLES

The embodiments of the present invention will be illustrated by the following set forth examples. All parameters and data are not to be construed to unduly limit the scope of the embodiments of the invention.

Example 1

Solution blends of PEA-Bz and the PEA of formula 3 can be prepared according to the following procedures. A first composition can be prepared by mixing PEA-Bz and the PEA of formula 3 in a ratio (w/w) of about 1:3 (“PEA-Bz blend”), resulting in an effective Tg of about 32° C. for the PEA-Bz blend, and then adding about 2% (w/w) of the PEA-Bz blend to absolute ethanol. A second composition can be prepared by adding everolimus to the first composition at a drug solid:PEA-Bz blend solution ratio (w/w) of about 1:500, which corresponds to a drug:PEA polymer solids ratio in solution of about 1:10. The above compositions can be agitated to hasten the dissolution process.

Example 2

An everolimus-containing medical article comprised of two layers can be fabricated from the compositions of Example 1 as follows. The second composition of Example 1 is sprayed onto the surface of a bare 12 mm VISION™ stent (Guidant Corp.) and dried to form a coating. An example coating technique comprises spray-coating with a 0.014 fan nozzle, a feed pressure of about 0.2 atm and an atomization pressure of about 1.3 atm; applying about 20 μg of wet coating per pass; drying the coating at about 62° C. for about 10 seconds between passes and baking the coating at about 50° C. for about 1 hour after the final pass to form a dry agent layer. The agent layer can be comprised of about 560 μg of the PEA-Bz blend and about 56 μg of everolimus. A second layer can be applied from the first composition of Example 1 by using the example coating technique. This topcoat layer can contain about 384 μg of the PEA-Bz blend. The total weight of the coating on the stent will be about 1000 μg.

Example 3

Solution blends of PEA-TEMPO and the PEA of formula 4B can be prepared according to the following procedures. A first composition, composition 1, can be prepared by mixing PEA-TEMPO and the PEA of formula 4B in a ratio (w/w) of about 1:1 (“PEA-TEMPO blend 1”), resulting in an effective Tg of about 39° C. for the PEA-TEMPO blend 1, and then adding about 2% (w/w) of the PEA-TEMPO blend 1 to absolute ethanol.

A second composition, composition 2, can be prepared by adding everolimus to the first composition at a solid drug:PEA-TEMPO solution blend ratio (w/w) of about 1:300, which corresponds to a drug:PEA polymer solids ratio in solution of about 1:6. The above compositions can be agitated to hasten the dissolution process.

Example 4

Solution blends of PEA-TEMPO and the PEA of formula 5C can be prepared according to the following procedures. A first composition, composition 3, can be prepared by mixing PEA-TEMPO and the PEA of formula 5C in a ratio (w/w) of about 2:1 (“PEA-TEMPO blend 2”), resulting in an effective Tg of about 39° C. for the PEA-TEMPO blend 2, and then adding about 2% (w/w) of the PEA-TEMPO blend 2 to absolute ethanol.

A second composition, composition 4, can be prepared by adding everolimus to the first composition at a solid drug:PEA-TEMPO solution blend ratio (w/w) of about 1:300, which corresponds to a drug:PEA polymer solids ratio in solution of about 1:6. The above compositions can be agitated to hasten the dissolution process.

Example 5

An everolimus-containing medical article comprised of two layers can be fabricated from the compositions of Examples 3 or 4 as follows. Composition 3 according to Example 3 or composition 4 according to Example 4 can be sprayed onto the surface of a bare 12 mm VISION™ Mstent (Guidant Corp.) and dried to form a coating. An example coating technique includes the step of spray-coating with a 0.014 fan nozzle, a feed pressure of about 0.2 atm and an atomization pressure of about 1.3 atm; applying about 20 μg of wet coating per pass; drying the coating at about 62° C. for about 10 seconds between passes and baking the coating at about 50° C. for about 1 hour after the final pass to form a dry agent layer. The agent layer can be comprised of about 336 μg of either the PEA-TEMPO blend 1 according to Example 3 or the PEA-TEMPO blend 2 according to Example 4 and about 56 μg of everolimus. A second layer can be applied from the composition 1 according to Example 3 or composition 3 according to Example 4 by using the example coating technique. This topcoat layer can contain about 400 μg of either the PEA-TEMPO blend 1 or the PEA-TEMPO blend 2. The two-layer medical article can be formed entirely of PEA-TEMPO blend 1 or PEA-TEMPO blend 2 or combinations thereof. The total weight of the coating on the stent will be about 792 μg.

While particular embodiments of the present invention have been shown and described, it will be obvious to those skilled in the art that changes and modifications can be made without departing from this invention in its broader aspects. Therefore, the appended claims are to encompass within their scope all such changes and modifications as fall within the true spirit and scope of this invention.

Yokoyama et al., Characterization of physical entrapment and chemical conjugation of adriamycin in polymeric micelles and their design for in vivo delivery to a solid tumor, Journal of Controlled Release 50:79-92 (1998).